Stent and method for manufacturing the stent

ABSTRACT

A stent includes a stent body having a circumference, a diameter of between approximately 4 mm and approximately 12 mm, in particular, 8 mm, and a length of between approximately 10 mm and approximately 250 mm, in particular, 150 mm, and struts disposed helically about the circumference in turns. Substantially circumferentially oriented connecting bridges connect respectively adjacent ones of the turns. A method for manufacturing a helical stent includes the steps of providing a stent body with struts disposed about the circumference thereof in turns and with bridges connecting the struts in adjacent turns. The stent body is expanded and, thereafter, some of the bridges, in particular, sacrificial bridges, are removed.

CROSS-REFERENCE TO RELATED APPLICATION

This application claims the priority, under 35 U.S.C.§119, of U.S.Provisional Patent Application No. 60/606,261 filed Sep. 1, 2004, theentire disclosure of which is hereby incorporated herein by reference inits entirety.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

n/a

FIELD OF THE INVENTION

The invention lies in the field of vascular stents. In particular, theinvention is in the field of helical stents for peripheral arteries, thebiliary tree, and other body lumens.

Stents have been developed for use in various lumens of the body,including the biliary tree, venous system, peripheral arteries, andcoronary arteries. Stents are used to open or hold open a lumen that hasbeen blocked (occluded) or reduced in size (stenosed) by some diseaseprocess, such as atherosclerosis or cancer. Previously developed stentsfor use in the biliary, venous, and arterial systems have been of twobroad classes: balloon-expanded and self-expanding. In both of theseclasses, stents have generally been made by two different techniques:either formed from wire or machined from a hollow tube. Othermanufacturing techniques have been proposed, such as vacuum or chemicaldeposition of material or forming a tube of machined flat material, butthose “exoti” methods have not been widely commercialized.

The vast majority of stents for use in the arterial and venous systemshave been made by machining a pattern of struts and connecting elementsfrom a metallic tubular preform (typically, by laser machining). Ofthese machined-tube stents, there have been two basic architectures:circumferential and helical. Circumferential configurations are basedupon a series of cylindrical bands joined longitudinally by bridges tomake a tubular structure. Helical configurations include a continuoushelical structure (typically made of an undulating pattern of struts andend-loops) with joining structures (referred to as “bridge”) joiningadjacent turns of the helix to provide mechanical integrity to thetubular structure (to prevent unwinding, kinking, and buckling).

Fine Cell Structure of Stents

Clinicians recommend the use of stents with relatively small openings tominimize the chances of friable material from the lumen wall penetratinginto the interior of the stent where it may result in narrowing of thelumen by cellular proliferation or where it may embolize downstream,causing damage or ischemia. U.S. Pat. No. 6,537,310 to Palmaz et al.teaches that it is advantageous to cover a stent with a porous filmhaving openings no larger than 17 microns in their smallest dimension tominimize the migration of embolic debris and plaque into the lumen of astent. However, Palmaz teaches use of a stent that is very difficult tomanufacture because of the great number of very small openings in thecovering film or “web.”

Clinicians have asked for stents with “thin, equi-spaced struts foroptimal wall coverage and drug elution” (“Clinical Impact of StentDesign: Results from 10 Years Experience,” C. DiMario, TCT2003). DiMariodemonstrates 15.0% restenosis versus 36.6% for stents with thin struts(50 microns, Multilink) versus thick struts (average of all stentsevaluated with struts greater than or equal to 100 microns). DiMarioalso relates stent efficacy to “integrated cell size,” showing betterresults for the BX VELOCITY® stent with cells of 3.3 mm² versus stentswith larger cell sizes. DiMario reports reduced neointimal hyperplasiafor smaller struts (0.8 mm thickness for closely-spaced 125-micronstruts versus 1.54 mm thickness for wider-spaced 200-micron struts).Because prior art stent designs have large gaps between stent parts,drug elution about these parts does not adequately cover all of thetissue within the bounds of the stent.

In “Clinical Impact of Stent Design: Results From Randomized Trials”(TCT 2003), A. Kastrati reports reduced residual percent-diameterstenosis after stenting (4.0% versus 5.7%) with 50-micron struts(Multi-link) versus 140-micron (Multi-link Duet).

In his report “Era of Drug-Coated and Drug-Eluting Stents” (TCT 2002),G. Grube states that the typical open-cell configuration gives poordistribution of the drug into the arterial wall because of the largeopen gaps when the stent is situated in a bend of the artery.

Number-of-Struts to Strut-Length Ratio

U.S. Pat. No. 6,129,755 to Mathis et al. (hereinafter “Mathis”) teachesimproved self-expanding stents with circumferential hoops of strutsjoined by oblique longitudinal bridges. Described therein is theimportance of having a large number of struts per hoop (the number ofstruts counted by going around the circumference) and minimum strutlength to minimize strains in superelastic materials and to preventemboli from passing through the wall of the stent. Mathis defines afigure of merit that is the ratio of number of struts around thecircumference to the length (in inches) of a strut, measuredlongitudinally. This ratio, which has the units of reciprocal inches,will be referred to herein as the M-D Ratio because the inventors wereMathis and Duerig. Mathis describes prior-art stents as having a ratioof about 200 and that their improved stent has an M-D Ratio of over 400.A representative stent produced by Cordis Corporation according to theMathis-Duerig invention—referred to as the “SmartStent”—has 32 strutsper circumference and strut lengths of approximately 0.077 inch,resulting in an M-D Ratio of approximately 416.

The M-D Ratio is determined by number of struts divided by strut length.For a given diameter stent, assuming “maximum-metal” configuration,which is typical for self-expanding stents, the number of struts aroundthe circumference is inversely proportional to the strut width. Thus,the M-D Ratio is inversely proportional to the product of strut widthand length.

SUMMARY OF THE INVENTION

It is accordingly an object of the invention to provide a helical stentand a method for manufacturing the stent that overcome thehereinafore-mentioned disadvantages of the heretofore-known devices ofthis general type and that improves helical machined-tube stents,whether balloon-expanded or self-expanding.

The self-expended stent of the present invention is suitable for use inperipheral arteries, the biliary tree, and other body lumens. Inparticular, it will be most advantageous for use in arteries whereflexure is an important factor, such as iliac arteries and carotidarteries. It is not traditional for cardiologists to use self-expandingstents in coronary arteries or coronary bypass grafts. Nonetheless, thepresent invention is especially suitable for the diffuse disease oftenencountered in these locations. Also, because of the high total surfacearea of the present configuration, the stent is particularly suitablefor the application of drug-eluting coatings intended to reducerestenosis or for other therapies. Specifically, the stent according tothe present invention allows virtually all tissue within the coveragearea of the stent to be in the elution areas. In particular, the stentprovides tissue coverage so that no element of wall tissue is more than350 microns to 400 microns away from the nearest strut. Such aconfiguration assures a short diffusion path from a strut covered with adrug-eluting agent to any portion of the tissue.

With the foregoing and other objects in view, there is provided, inaccordance with the invention, a stent, including a stent body having acircumference, a diameter of between approximately 4 mm andapproximately 12 mm and a length of between approximately 10 mm andapproximately 250 mm, and struts disposed helically about thecircumference in turns. Substantially circumferentially orientedconnecting bridges connect respectively adjacent ones of the turns.

With the objects of the invention in view, there is also provided astent, including a stent body having a circumference, an expanded state,and struts disposed helically about the circumference in turns anddefining an outer circumferential cylinder in the expanded state.Substantially circumferentially oriented bridges connect adjacent onesof the turns. The bridges rae raised from the outer circumferentialcylinder when the stent body is in the expanded state.

With the objects of the invention in view, there is also provided astent, including a stent body having a circumference, struts disposedhelically about the circumference in turns, the turns defining a helicalgap therebetween, and circumferentially oriented bridges connectingadjacent ones of the turns across the helical gap.

In accordance with another feature of the invention, the diameter isbetween approximately 4 mm and approximately 8 mm.

In accordance with a further feature of the invention the length isbetween approximately 25 mm and approximately 150 mm.

In accordance with an added feature of the invention, the struts ares-shaped and have straight portions and curved portions connectingrespectively adjacent ones of the straight portions.

In accordance with an additional feature of the invention, the stentbody has an expanded state, the struts define an outer circumferentialcylinder in the expanded state, and the connecting bridges are raisedfrom the outer circumferential cylinder when the stent body is in theexpanded state.

In accordance with yet another feature of the invention, the stent bodyhas an expanded state, the struts define an outer circumferentialcylinder in the expanded state, and the connecting bridges form bumpsradially extending outside the outer circumferential cylinder when thestent body is in the expanded state for anchoring the stent body whenimplanted.

In accordance with yet a further feature of the invention, the stentbody has a non-expanded state and an expanded state, and the connectingbridges are circumferentially oriented in the expanded state.

In accordance with yet an added feature of the invention, the stent bodyhas a non-expanded state and an expanded state, and the connectingbridges are circumferentially oriented in the non-expanded state and theexpanded state.

In accordance with a concomitant feature of the invention, the turnsdefine a helical gap therebetween, and the bridges connect the adjacentones of the turns across the helical gap.

The present invention relies on a helical configuration with muchshorter struts and significantly higher number of struts around thecircumference than the prior art. Indeed, helical stent configurationsaccording to the present invention are not limited to even-integralnumbers of struts—as are “hoop” configurations taught by Mathis. Infact, odd-integral numbers of struts around the circumferential or evennon-integral numbers of struts around the circumference are possible inthe helical configuration of the present invention because there is norequirement for the struts to rejoin themselves to make complete hoops.In other words, a helical stent could have 31.567 struts per revolution,or any other arbitrary number. Mathis teaches that increasing the M-Dratio increases the rigidity of a stent, yet the rigidity of twocomparative stents bears this relationship only if the stents beingcompared are expanded to comparable opening angles between the struts.In fact, with commercially available stent product lines produced to theM-D configuration, stents of different diameters frequently have thesame number of struts. Even so, such a configuration family has smalleropening angles in smaller sizes than in larger sizes; this is becausesimilar stent preforms are used to make a range of final stent sizes.The smaller stents in a product family sharing the same preformconfiguration (including the number of struts) have smaller openingangles, of course, resulting in lower chronic outward force (COF) andlower radial resistive force (RRF) to collapse, because the effectivebending-lever length is longer in struts with lower opening angles.Mathis teaches M-D Ratios of over 400 and numbers of struts up to 32 ormore but does not teach or suggest ratios of near or over eight-hundred(800), let alone over one thousand (1000). Mathis, specifically, doesnot mention what effects a much larger number of struts would have, anddoes not imply implementation of significantly shorter struts.

In the present invention, an exemplary configuration for an 8 mmdiameter stent incorporates 46 struts around the helical circumferenceand the struts have a length of approximately 0.99 mm (0.039 inches).The M-D Ratio for this exemplary configuration according to the presentinvention is, therefore, 1180—nearly three times the ratios taught inthe prior art. Stents according to the present invention have new andunexpected properties, even though they require greater attention toopening angles (and, hence, have a more limited useful size range for agiven configuration).

In comparison with prior art stents having cells of 3.3 mm², the presentinvention gives an integrated cell size of 1.6 mm² per cell unit in an 8mm diameter stent. In a configuration with bridges every three cellunits, the total integrated cell size would be 4.8 mm², which isproportionately smaller than that of the BX VELOCITY®3 mm stent.

Specifically, configurations according to the present invention havemuch smaller openings when expanded and, particularly, when the expandedstent is flexed in bending. The substantially smaller openings result ingreatly improved resistance to the passage of emboli through the stentwall.

Another characteristic of stents according to the present invention is agreatly increased flexibility and resistance to buckling in bending ortorsion. Stents according to the present invention also have improvedfatigue life in real-life applications, resulting from a large number ofstruts and bending segments to absorb irregular, localized deformationscaused by the anatomy—as opposed to such local deformations being placedon a small number of struts and bending segments, which results inover-straining some of these elements.

Stent configurations optimized for a particular expanded diameter willhave struts as wide as possible, consistent with the maximum allowablestrain during storage and compression. The result of such a criterion isthat stent configurations according to the present invention, with agreater number of struts of shorter length and narrower width than priorart configurations, will allow greater bending deflections, resulting ingreater possible opening angles. Constructing an expanded stent withgreater allowed opening angles also results in a relatively shorterprojected lever-arm length acting on the struts and bending segmentswhen the stent is expanded in the anatomy. These shorter lever armsresult in higher outward forces applied to the vessel walls when thestent is expanded.

It should be noted that the present invention results in configurationsthat are optimized for a small range of expanded sizes, creating theneed to have individualized configurations for each expanded size ofstent. This approach deviates from the prior art and results in higherconfiguration and validation costs, but results in stents withsignificantly improved flexural and fatigue properties while, at thesame time, providing optimized radial outward forces and collapseresistance for each size.

Another characteristic of stents made according to this invention is theincreased difficulty of collapsing the stent when preparing it forinsertion into a delivery catheter. The struts of stents made accordingto the present invention are proportionately narrower and, hence, lessstiff in bending (in proportion to the cube of the width of the struts)when compared to prior art stent designs. This decrement in stiffnessmay be offset by increasing the opening angle of the stent, as describedelsewhere herein, but the reduced stiffness of the struts (and also theincreased opening angles) results in a tendency for portions of thehelix to buckle when subjected to the stresses and strains required tofully collapse the stent prior to insertion into its delivery system.The result of this buckling is that a series of struts and loops forminga portion of the helical winding will resist collapsing uniformly alongthe helical axis, but rather buckle away from the helical axis (usuallyremaining in the plane of the cylindrical surface of the stent). When aportion of the helix buckles, the struts of that turn may begin tointerfere or interdigitate with the struts of an adjacent helical turn.Thus, stents made according to the present invention are more difficultto compress into their delivery system.

This tendency for a series of struts and loops to buckle away from thehelical axis is aggravated when the struts are very narrow, when theopening angles are higher, and when there is a long series of strutsbetween the connecting bridges. The presence of the connecting bridgesthat join adjacent turns of the stent stabilizes the stent duringcompression; this stability is greater when there are only a few strutsbetween bridges, and the stability is reduced when there is a largenumber of struts between bridges. For example, stents made with seriesof seven or nine struts between bridges have a high tendency towardbuckling when compressed; stents made with five struts between bridgeshave an intermediate tendency toward buckling when compressed; and,stents with only three struts between bridges have a low tendency towardbuckling when compressed. It should be noted that this tendency towardbuckling does not adversely affect the characteristics of the stent whenexpanded in the body, because the compressive strains experienced in thebody are insufficient to cause the buckling seen during compression intothe delivery system. However, it has been found that stents with verylow numbers of struts between bridges (e.g., one or three), though theyare very easy to fully compress, do not have flexibility as great asthat of stents with larger numbers of struts between bridges (e.g.,seven or nine). As a result, it has been found that there is a tradeoffbetween design choices which create a stent that is easy to compressversus choices which make the stent flexible. It has been found thatstents made according to this invention, configured with an M-D ratio inthe range of 1000, have the most favorable balance of flexibility andbuckling during compression when the number of struts between bridges isin the range of three to five.

Other features that are considered as characteristic for the inventionare set forth in the appended claims.

Although the invention is illustrated and described herein as embodiedin a helical stent and a method for manufacturing the stent, it is,nevertheless, not intended to be limited to the details shown becausevarious modifications and structural changes may be made therein withoutdeparting from the spirit of the invention and within the scope andrange of equivalents of the claims.

The construction and method of operation of the invention, however,together with additional objects and advantages thereof, will be bestunderstood from the following description of specific embodiments whenread in connection with the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a fragmentary, enlarged partially cross-sectional andpartially plan view of a stent delivery system configured to implant astent according to the invention in a vessel;

FIG. 2 is a fragmentary, enlarged plan view of the stent of FIG. 1expanded and implanted in the vessel;

FIG. 3 is a fragmentary, enlarged plan view of a portion of a firstembodiment of the stent of FIG. 1;

FIG. 4 is a fragmentary, enlarged plan view of a portion of a secondembodiment of the stent of FIG. 1;

FIG. 5 is a fragmentary, enlarged plan view of a portion of the secondembodiment of the stent of FIG. 4 with circular markers;

FIG. 6 is a fragmentary, enlarged plan view of a portion of the firstembodiment of the stent of FIG. 3 with flat-ended markers;

FIG. 7 is a fragmentary, enlarged plan view of a further enlargedportion of the first embodiment of the stent of FIG. 3 with somesacrificial bridges removed;

FIG. 8 is a fragmentary, side elevational view of a portion of anexpanded stent according to the invention with a protruding bridge;

FIG. 9 is a fragmentary, enlarged plan view of a further enlargedportion of the first embodiment of the stent of FIG. 7 with thesacrificial bridges having break points;

FIG. 10 is a plan view of a flat cut pattern representing thelaser-cutting path to be created around a circumference of tubing fromwhich the stent according to the invention is to be created;

FIG. 11 is a fragmentary, enlarged, perspective view from the side of astent according to the invention;

FIG. 12 is a fragmentary, further enlarged, perspective view of aportion of the stent of FIG. 11;

FIG. 13 is a fragmentary, enlarged, perspective view from an end of thestent of FIG. 11;

FIG. 14 is a fragmentary, further enlarged, perspective view of aportion of the stent of FIG. 13;

FIG. 15 is a fragmentary, enlarged plan view of a portion of an expandedstent according to the invention illustrating a largest embolism area;and

FIG. 16 is a fragmentary, enlarged plan view of a portion of a prior artstent illustrating a largest embolism area.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

Referring now to the figures of the drawings in detail and first,particularly to FIG. 1 thereof, there is shown is a helical stent 1according to the present invention fitted on a delivery catheter 20 ofan exemplary delivery system 10. The helical stent 1 is about to beimplanted in a vessel 30. The helical stent 1 is in its unexpanded stateand loaded into/onto the delivery system 10 that has traveled to animplantation site. FIG. 2 illustrates the helical stent 1 implanted inthe vessel 30 after being expanded, whether by a balloon of the catheter20 or by self-expansion due to a shape memory of the material of thestent 1.

The helical stent 1 has proximal 2 and distal 3 ends—defined by a bloodflow direction A. The helix of the stent 1 can be a single coil with onestart at the proximal end that winds all the way to the distal end. Sucha configuration is possible with the present invention because thehelical stent 1 has very short struts, which will be explained infurther detail below. Another configuration alternative usable withshort struts is a multiple-helix configuration (shown in FIG. 2), wheremore than one helixed start is present, for example, a double-lead, atriple-lead, and so on. With an exemplary 8 mm size of the helical stentaccording to the present invention, up to 4 leads are practical.

FIGS. 3 and 4 show enlarged views of a portion of the body of thehelical stent 1 of the present invention. Each turn 4 of the helix isformed, in a preferred embodiment, by a continuous repetition ofs-shaped struts 5 throughout the length of the helix. The struts 5 havestraight portions 6 and curved portions 7 connecting respectivelyadjacent straight portions 6. Connecting bridges 8 have a widthsubstantially similar to a width of the straight and curved portions 6,7 and connect adjacent turns 4 of the helix. Also connecting adjacentturns of the helix are sacrificial bridges 9, which have a width smallerthan a width of the straight and curved portions 6, 7. Both of thebridges 8, 9 will be described in greater detail below.

Stents 1 may be made according to the present invention with struts 5that are aligned with the longitudinal axis 10 of the stent 1, as shownin FIG. 3, or the struts 5 may be aligned perpendicular to the helicaldirection 11, as shown in FIG. 4. There are advantages and differencesto both configurations. The longitudinally aligned straight portions 6of the struts 5 produce a stent 1 that requires lower force to deployfrom a confining sleeve because there are no oblique, twisting,knife-edges to cut into or grip the sleeve. One characteristic of thisembodiment, is that the struts 6 are not of equal length (there is anequal number of short and long struts) and, therefore, it is notpossible to fully balance the flexibility of these struts to fullyutilize the properties of the material used to build the stent 1. Incomparison, the configuration shown in FIG. 4 with helically alignedstraight portions 6 of the struts 5 has the advantage of equal strutlengths. This configuration, in comparison, has a higher friction whenthe stent 1 is engaged inside a deployment system.

Other advantages and differences exist for these two configurations,including ease of manufacture, ease of inspection, and stability duringexpansion or deployment of the longitudinal and helically aligned strutconfigurations. But, either may be used to practice the teachings of thepresent invention.

Lollipop Crown and Retention Levers

It is customary to provide radiopaque markers on stents so that they canbe easily visualized by using x-rays for assisting their placement anddeployment. The present invention provides a convenient area at which tolocate these markers, specifically, beyond the ends of the helicalpattern of struts. If the markers 12 are paddle-shaped (that is, havinga substantially disk-like enlarged portion with a narrow extension thatjoins it to the structure of the stent), they may be attached to theends of the 180-degree bending segments 7 (or to other locations on thebending segments 7 or straight portions 6). It is advantageous todispose the markers so that a paddle with a short extension is locatednear the end of the helix (the extreme end of the helical pattern) andpaddles on longer connectors are located at other locations around thecircumference. In such a configuration, the extreme ends of the paddlesare even, providing a relatively planar end to the stent 1. However, themarker portions 12 need not be paddle-shaped. They can merely berod-shaped to extend away from either or both of the distal and proximalends 2, 3 of the stent 1. These rods can be expanded for better seatingin the vessel and, even with a smaller surface area as compared to thepaddle-shaped markers, can still provide sufficient area for receivingindicators that allow for better imaging.

The flat end provided by the paddle-shaped markers 12 of FIG. 6, forexample, facilitates pushing the stent 1 out of a deployment device(although a shaped pusher that conforms to the helical end of the stentcould be used but is harder to manufacture and align). During deploymentof a self-expanding stent, a pusher component of a delivery catheterexerts a (distally-directed) counter-force onto the proximal end of thestent while a covering sleeve is retracted from its position over thestent. As the covering sleeve is retracted relative to the stent and thepusher, the distal end of the stent is exposed and, therefore, expandsto contact the interior of the vessel. Thus, it is important for thepusher to be able to apply evenly the distally directed force onto theproximal end of the stent during deployment. Also, for most medicalindications, physicians prefer stents with flat ends substantiallyperpendicular to the longitudinal axis of the device so that there is aneven transformation from the end of the stent to the unsupported(unstented) portion of the vessel wall.

The paddle shaped markers 12 described above can be spaced from thehelical end of the stent by narrow connectors as shown in FIGS. 5 and 6,or by full-width connectors (i.e., markers that are of uniform widthfrom their ends to the point where they join the struts or loops of thestent), or by directly connecting them to the other elements of thestent. FIG. 5, for example, illustrates three paddle-shaped markers 12attached by narrow connectors to the helical end of a portion of a stent1.

While the disk-like enlarged portions of paddle-shaped markers 12 can berounded, it is preferable for the extreme outer ends to be relativelystraight. As such, the paddle-shaped markers 12 may be provided withnon-circular ends 13 to facilitate engagement of the pushing device ofthe deployment catheter with which the stent is implanted. For example,FIG. 6 shows flat-ended paddle-shaped markers 12 that maximize contactbetween the paddles and the pushing device.

In addition, the paddle-shaped markers 12 may be used to help anchor thestent 1 during and after deployment. Specifically, the paddles may beradially expanded further than the struts 5, 6, 7 so that they form afunnel-shaped end to the stent 1 once expanded.

While the present drawings show paddle-shaped markers without separateradiopaque inserts, it should be noted that pieces of radiopaquematerials, such as tungsten, tantalum, molybdenum, platinum, or gold,might be inserted into the markers to enhance their visibility underx-rays. For example, inserted cylinders of tantalum 0.50 millimeters indiameter and having a thickness equal to or less than that of the markerpaddles, may be pressed, glued, riveted, threaded, or otherwise attachedinto holes or depressions formed in the paddles.

Circumferential Bridges and Fixation Structures

According to the present invention, there is an array of connectingbridges 8 that connect adjacent turns or columns of struts 4 to providethe desirable overall stent flexibility as well as structural integrity.It is advantageous to form these bridges 8 in a substantiallycircumferential direction, as shown in FIG. 7. Two advantageouscharacteristics emerge by so forming the connecting bridges 8. First,the vertical (circumferential) offset caused by the bridges 8 ensuresthat, after expansion, the adjacent 180-degree bending segments (thevertices of the expanded strut pairs) are offset from one another and,thus, will interdigitate, allowing the stent 1 to bend easily. Second,these circumferential bridges 8 are curved sharply in the planeperpendicular to the axis 10 of the stent 1, which curvature resultsfrom the stent 1 being formed from small-diameter tubing. By carefulcontrol of the expansion process, it is possible to expand the stent 1while retaining substantially all of the curvature of these bridges 8.In the resulting expanded stent 1, these bridges 8, then, extendradially away from the cylindrical surface of the stent 1 and presentedges perpendicular to the axis 10 of the stent 1. Thus, during andafter implantation, these features engage the vessel or body lumen wall30, preventing migration of the stent 1. The enlargement of a bridge 8in FIG. 8 illustrates how these structures protrude beyond the wall of astent 1 in this manner.

Multi-Mode Markers for Ultrasound, X-Ray, and MRI

Customarily, radiopaque materials such as gold, tantalum, zirconiumoxide, barium and bismuth salts, hafnium, molybdenum, etc., are attachedto stents to enable visualization by x-rays. The present invention issuitable for incorporating such markers, especially at the location ofthe paddles 12, 13, as described above.

In addition to the prior-art use of radiopaque markers, it is possibleto use other types of fiducial markers to enable placement, deployment,and subsequent location and diagnosis of the stent 1. Specifically,other non-illustrated markers can be made that are easily imaged byultrasound, such as abraded surfaces, holes, voids, porous materials andcoatings, hollow balloons, and layered materials of different sonicproperties, to name a few. For example, a hole 0.50 millimeters indiameter may be filled with a composite consisting of glassmicroballoons and tungsten powder suspended in an epoxy matrix. Such acomposite marker would be highly visible under ultrasound imaging aswell as x-ray imaging. Additionally, markers having varying textureshave improved anchoring characteristics.

Magnetic resonance imaging may be enhanced by inclusion of paramagnetic,diamagnetic, and ferromagnetic materials that locally change themagnetic-field-producing spin-energy transitions in odd-number nucleisuch as hydrogen, carbon-13, fluorine-19, and other nuclides known tothose skilled in the art of magnetic resonance imaging. Specifically,small pieces of gadolinium or gadolinium salts (paramagnetic) providevisible changes to the image formed by hydrogen nuclei in theirvicinity, thus, such materials can be incorporated into fiducialmarkers. Nano-scale ferromagnetic materials, such as hematite or otheroxides, can also provide useful MRI artifacts without troublesome imagedistortion.

Magnetically active elements, salts, and compounds can be incorporatedindividually or in combination with other marker materials, such asradiopaque materials or ultrasound-visible structures or materials, tomake multi-mode markers. Composite markers may contain materials withmagnetic properties suitable to present fiducial marks on images made bymagnetic resonance imaging (MRI) as well as other imaging modalities.Examples include combinations of radiopaque materials (such as, tungstenpowder, zirconium oxide, bismuth subcarbonate, and gold powder),magnetically active materials such as diamagnetic or ferromagneticmaterials (including gadolinium foil and powder, gadolinium salts,nanocrystalline iron oxide, and iron powder, for example), andultrasonically visible material such as glass or ceramic microballoons.

Manufacturing

The standard method for manufacturing machined tubular metal stents isto begin with a small-diameter metallic tube, typically, of stainlesssteel, platinum alloy, or chromium-cobalt alloy for balloon-expandedstents and of a nickel-titanium alloy for self-expanding stents. Thistubing is mounted in a laser machining system that rotates the partaround a stationary axis so that the focal point of a laser beamimpinges upon the surface of the tube. When laser power is applied alongwith a coaxial jet of gas (either air, oxygen, or an inert gas such asargon), the material is perforated by the laser energy (and possiblyassisted by chemical reaction with air or oxygen). The tubing is movedunder the laser beam in at least two axes, rotational and longitudinal,so that a continuous cut (or kerf) is made while the laser energy isapplied. The laser beam is switched on and off under computer control incoordination with the longitudinal and rotational motions so that adiscontinuous pattern of cuts is applied to the tubing.

Following the laser-cutting operation, excessive material is removedfrom the interior and exterior surfaces of the tubing, and the tubing isfurther processed to produce either a balloon-expandable or aself-expanding stent. In the case of a balloon-expandable stent, thelaser-cut tubing preform is polished and cleaned using a combination ofchemical, mechanical, and electrochemical measures to produce a finishedstent that is, then, for example, crimped onto a balloon catheter. Inthe case of a self-expanding stent, the laser-cut tubing is expanded byforcing it onto a succession of larger and larger mandrels. At each stepof expansion, the tubing is subjected to an appropriate heat-treatingstep to thermally set the expanded step. For example, nickel-titaniumtubing may be heat treated at 480 degrees Celsius (480° C./896° F.) forthirty seconds while expanded on a mandrel to set that stage ofexpansion. Typically, two to six expansion stages are necessary to fullyexpand a nickel-titanium self-expanding stent. After expansion, thestent is finished by a combination of chemical, mechanical, andelectrochemical polishing to produce a smooth, biocompatible surfacesuitable for implantation. The finished stent is, then, chilled (totransform it to the soft and deformable martensitic condition) andcompressed radially to a size small enough to be placed into catheter ofthe stent delivery system.

The Importance of Uniform Expansion During Manufacturing

One manufacturing problem that must be overcome with self-expandingstents having the fine structures as described in the present inventionis uneven opening occurring during thermo-mechanical expansion of theas-cut tubing to the final, expanded stent. The standard manufacturingprocess involves stretching the laser-cut stent over progressivelylarger tapered-end cylindrical mandrels and heat-treating the materialat several stages while supported by these mandrels. The stent can beexpanded by stretching it onto the successive expansion mandrels eitherat a low temperature (in the soft, martensitic condition) or at ambienttemperature (in the springy, austenitic condition). Once expanded onto amandrel, the stent is exposed for a short period (several seconds to afew minutes) of high temperature, typically in the 450 to 500 Celsiusrange, to “shape-set” or anneal the stent at that level of expansion.

While the expansion process has been well understood by stentmanufacturers in the past, it is problematic because great care must beexercised to make sure that no portion of the stent is over-strained(over-stretching or over-bending) during the stages of expansion.Over-straining can damage permanently the superelastic material of whichthe stent is formed (typically a nickel-titanium superelastic alloy),resulting in hidden defects within the material that might causeimmediate fracture or, worse, fatigue failure after the stent has beenimplanted. Therefore, manufacturers typically expand stents in severalfractional steps, and may employ elaborate measures, either by humanskill or tooling, to prevent any portion of the stent from beingover-strained. Over-straining is most commonly seen as a pair of strutshaving an unusually large opening angle at their vertex relative to theangle of other strut pairs in the vicinity. This condition must becontrolled and identified by in-process inspection because it may behidden by later expansion steps and because it is an inherently unstablecondition. That is, during a given expansion step, once a pair of strutsbegins to open excessively, that vertex becomes weakened, and theopening strains tend to be further concentrated on that particular pairof struts, so that it becomes progressively more over-strained.

Sacrificial Bridges

The present invention provides a process for preventing this localover-straining. In the present invention, as compared to the originalnumber of bridges 8, 9 originally existing between adjacent columns (orhelical turns) of strut pairs in the unfinished stent, only a fewbridges 8 exist in the finished stent, which remaining bridges 8 providethe desired flexibility and resistance to fatigue. In the as-cutcondition and during the steps of expansion, additional sacrificialbridges 9 connect the bending segments joining strut pairs in adjacentturns or columns. Thus, when the stent 1 of the present invention isbeing expanded, it has greatly improved robustness, and each pair ofstruts is connected at the maximum number of points to adjacent parts ofthe expanding stent. What is referred to herein as sacrificial bridges 9provides these additional connections and causes the expansion strainsto be much more evenly shared by all the elements of the stent, whichsharing results in a significant increase in the evenness of strainsduring expansion. The result is an expanded stent with vertex openingangles that have much less variation.

It is true that the sacrificial bridges 9 substantially reduce theflexural (bending) flexibility of the stent 1. Thus, they must beremoved prior to finishing the stent 1. These sacrificial bridges 9 maybe removed at any stage after expansion, but, preferably, they areremoved immediately after the final expansion heat-treating step, priorto any material-removal or polishing steps, so that any burrs left byremoval will be reduced or eliminated during the polishing steps.Alternatively, the sacrificial bridges 9 may be removed after some ofthe expansion stages, but prior to one or more final expansion stagebecause it has been found that, once the stent 1 has been partiallyexpanded in a very even manner, subsequent expansion steps do notgenerally introduce unevenness among the opening angles. In any case, itis only necessary to remove the extra, sacrificial bridges 9 at somepoint prior to implantation so that the finished stent 1 has the desiredflexibility in its final, implanted form.

Bridge Removal Processes

To facilitate removal of the sacrificial bridges 9, special features canbe engineered into the as-cut structure to provide prescribed locationsfor cutting or breaking the sacrificial bridges 9. These features areillustrated in FIG. 9 as, for example, notches 14 formed at one or bothof the ends of the sacrificial bridges 9 connected to the struts ofadjacent turns 4. While providing notches 14 is only one example to formthe cutting/breaking location, alternative exemplary methods of removingsacrificial bridges include chemical etching, abrasive blasting,grinding, electrochemical etching or polishing, shearing, or lasercutting.

Final Burr Removal Processes

Customarily, stents are finished by a combination of abrasive blasting,glass-bead honing, chemical etching, mechanical polishing, andelectrochemical polishing. All of these processes assist removal of anyremaining burr left by the removal of the sacrificial bridges 9. Inaddition, other measures, such as grinding, shearing, mechanicalpolishing, and cutting may be used to locally smooth and remove burrsleft by the sacrificial bridges 9.

FIG. 10 illustrates a flat cut pattern representing the laser-cuttingpath that will be created around the circumference of tubing from whichthe stent 1 is to be made. For clarity, the pattern in FIG. 10 is brokenalong a longitudinal line to represent it as a flat, two-dimensionalpattern. In practice, however, this two-dimensional flat pattern(representing width and length) is transformed into a two-dimensionalcylindrical pattern (representing rotation and length) by theprogramming of the computer-controlled laser-cutting machine so that thecut pattern is arrayed continuously around the cylindrical surface ofthe tube. The resulting cut pattern produces a cylindrical or helicalarray of struts 5 to form the stent 1.

FIGS. 11 to 14 illustrate a portion of a stent 1 according to theinvention with the s-shaped struts 5 oriented in the configuration shownin FIG. 3, i.e., the straight portions are substantially aligned withthe longitudinal axis of the stent 1 before expansion. In FIGS. 11 to14, the right end of the stent is not depicted and the left end is shownwith flat-ended markers 13 extending from respective curved portions 7.The narrow portions of the markers 13 do not have the same length and,therefore, the extreme left flat ends of the markers 13 align along asingle planar surface orthogonal to the longitudinal axis of the stent 1once the stent is expanded. The embodiment of FIGS. 11 to 14 shows thestent 1 in an expanded state after the sacrificial bridges 9 have beenremoved. As can be seen in each of FIGS. 11 to 14, the bridges 8 alignalong a circumference of the interior cylinder defined by the stent 1.The exemplary embodiments of FIGS. 3 to 7 and 9 to 10 show the helicaldirection 11 of the struts 5 as “left-handed” (the helical direction 11advances helically to the left) and the advancing direction of thebridges 8,9 as “right-handed” (the advancing direction of the bridges 8,9 is opposite the helical direction 11). The exemplary embodiment shownin FIGS. 11 to 14, in comparison, shows the helical direction 11 asright-handed and the direction of the bridges 8, 9 as left-handed. Theinterior cylinder depicted in FIGS. 11 to 14 is only presented forillustrative purposes.

Using Very Narrow Kerfs in Stents with High Strut Count

It has been discovered that the manufacture of the stent 1 according tothe present invention, in particular, the laser cutting and expansionsteps, are made substantially more difficult when the size of struts 5is reduced and the number of struts 5 is increased. For example, it hasbeen found that normal laser cutting processes yield a finished kerfwidth (after material removal processes needed to provide a stent withthe desired polished finish) of approximately 25 to 40 microns. If, forexample, a total of 46 struts were disposed around a circumference, thenthe total circumferential width of kerfs would be at least 46×25microns, or 1150 microns (1.15 millimeters). Of this kerf space, half isnot collapsible during compression of the stent, because half of thekerfs are at the inside of the 180-degree bends that join the ends ofthe struts. Hence, a stent of the current configuration made byconventional manufacturing processes has at least 0.57 millimeter ofincompressible circumference resulting from the kerfs at the 180-degreebends (corresponding to 0.18 millimeter of diameter reduction). However,by reducing the total kerf from 25 microns to 18 microns according tothe present invention, the diameter after compression is reduced by 0.05millimeters—a significant difference in fully collapsed diameter.Moreover, by reducing the kerf from the conventional 25 microns to 18microns, a further advantage is obtained—the remaining strut widths areincreased due to the fact that less metal is removed. In the presentexample, reducing total kerf loss from 25 microns to 18 microns,assuming a pre-cut tubing diameter of 2 millimeters and 46 struts, theresulting strut width increases from 112 microns to 119 microns,resulting in a relative stiffness of (119/112)³, or 120%, becausestiffniess is proportional to the cube of width.

The use of these very narrow kerfs is particularly advantageous to thepresent invention because of the large number of struts 5 in theconfiguration—strut counts from 36 to 50, as compared with traditionalstents customary strut count, typically in the range of 24 to 32.

Cell Opening Size

The maximum embolus size that can pass through the wall of an expandedstent is determined by the size of the openings between the straightportions 6 and bending segments 7. More precisely, the maximum embolussize is described by the largest circle that can be inscribed within theopenings of a particular stent in its open configuration. It is,therefore, desirable to minimize the maximum embolus size to preventadverse results of embolization in patients.

Referring to FIG. 6 of U.S. Pat. No. 6,129,755 to Mathis et al. (whichis hereby incorporated by reference in its entirety), it can be seenthat the maximum size embolus that can be passed through the openingsbetween struts has a diameter described by the largest circle that canbe inscribed within the space between two adjacent struts and the vertexof a strut pair on the adjacent column of struts. The volume of such anembolus is proportional to the cube of the diameter. So, it can be seenthat the volumetric size of the largest embolus that can pass throughthe stent wall becomes smaller by the third power as the strut geometryis proportionally reduced in size (assuming otherwise similar geometryof the strut openings). From this analysis, it can be appreciated thatthe clinical effect of emboli can be substantially reduced by using agreater number of shorter struts; hence, clinical safety increasessharply with increases in the M-D Ratio, particularly in regions of thevasculature, such as the carotid arteries, where emboli are poorlytolerated and can have significant deleterious effects upon the patient.

An expanded helical stent 1 according to the present invention hasopenings sized to prevent a body (for example an embolus or asubstantially spherical body) of greater than approximately 800 micronsin diameter from passing therethrough. In a preferred configuration, theexpanded helical stent 1 according to the present invention contains 46struts of 120-micron width and 1000-micron length, for example. Such aconfiguration results in openings that would allow an inscribed circle15 of 610 microns. This feature is illustrated in FIG. 15. Bycomparison, the Cordis 8 mm×50 mm SmartStent allows a much largerinscribed circle. FIG. 16 shows the best-case alignment of the alternaterows of the struts in the SmartStent, allowing an inscribed circle 16 of1080 microns. The volume of an embolus of 1080 microns versus that of a610-microns embolus is 5.5 times larger. Thus, it can be seen that thepresent invention allows a much-increased ability to prevent the passageof clinically significant emboli through its pores.

Another advantage of the present invention in prevention of embolizationis realized in the case where the stent 1 is implanted in a bent, ornon-straight, configuration. In prior-art stents, bending causes openingof the space or gap between adjacent turns 7 or straight portions 6 ofstruts on the outside of the bend. Because the present invention teachesthe use of very short struts (on the order of between approximately 600and 1200 microns in length) and, hence, a shorter helical pitch orcolumn-to-column distance, a bending deformation to a stent results inopening of the gaps between several adjacent turns or columns of struts4. Thus, the distance by which any given gap is widened is reduced inproportion to the number of gaps involved. For example, a stent 1 withstruts 5 that are half as long will have twice as many gaps affected bya bend, and the widening of each of these gaps will be reduced by afactor of two.

Smooth Stiffness Gradient from High Bridge Frequency

Because stents 1 made according to the present invention have arelatively high number of features compared with stents made accordingto the prior art, and because there is a larger number of thesefeatures, including the straight portions 6 and the 180-degree loops 5that provide local flexibility as well as the bridges 8 joining adjacentturns or columns of struts 4 that provide structural integrity to theoverall structure, it is possible to fine-tune the flexibility andcompression/expansion properties to a much finer extent than inprior-art stents with a substantially smaller number of features. Atypical prior-art stent of the same size, for example, the Cordis 8mm×50 mm SmartStent, has approximately 700 struts. In comparison, forexample, an 8-millimeter diameter, 50-millimeter long stent 1 accordingto the present invention has approximately 1500 struts—more than a 100%increase.

It is possible to adjust the size and width of struts 5 along the lengthof the stent 1. However, the present invention allows for much moreprecise use of this conventional construction technique—because thefeatures of the stent 1 are smaller, there are more of them and, thus,the designer has a greater number of features over which to create agradient of properties such as stiffness, radial outward force, flexuralstiffness, surface area (for drug-coating application), and diameter.

In a similar manner, because of the large number of connecting bridges8, 9 in the configurations taught by the present invention, it ispossible to introduce other property gradients along the length of thestent 1. Among the properties affected by bridge frequency and locationare flexural stiffness and torsional stiffness. Therefore, it ispossible to construct a stent with greater torsional rigidity in thecentral portion than in the ends, or vice-versa. Similarly, it ispossible to provide the stent 1 with more bending flexibility at itsends (and, hence, lower stresses applied to the vessel walls) than inthe central segment by placing fewer connecting bridges 8, 9 at the endsof the stent 1 than in the middle. (Of course, the opposite possibilityalso exists, providing a stent 1 with stiff ends and a more flexiblecentral segment, suitable for use in an area of the body where flexiontakes place.)

Short-Pitch Helix

Also, it can be seen that the short length of struts 5 results in agreater helix angle (or, a helical axis more closely approachingperpendicular to the longitudinal axis) for a given circumference ofstent because the shorter struts 5 result in a reduced helical pitch.There are several advantages to such an increase in helix angle. First,the unevenness of the distal and proximal ends of the stent is reducedbecause the step where the end of the helix joins the previous turn issmaller (approximately equal to the strut length). Such a reduced stepprovides for a stent 1 with a substantially square-cut end (as istypically desired by physicians) in an easier manner.

Second, the increased helix angle results in a stent 1 that has areduced tendency to twist as it is expanded. It can be easily imaginedthat a helical stent with a very low helix angle, similar to acorkscrew, would tend to wobble and twist when released from a confiningsheath. As the helix angle is increased toward perpendicular (byreducing the strut length or helical pitch), a helical stent behavesmore and more like a non-helical stent constructed of joined cylindricalhoops, resulting in even, non-twisting behavior as it expands whenreleased. Even though some of the resulting properties of a stent with ahigh helix angle approach those that are advantageous in a non-helicalstent (such as a nearly square end and resistance to twisting duringexpansion), the advantageous properties intrinsic to a helical stent aremaintained, such as greater design freedom, lack of distinct rigid andflexible zones along the length of the stent, and more-uniformdistribution of applied stresses and strains.

As set forth above, another configuration alternative that becomespracticable with the very short struts 5 of the present invention is theemployment of a multiple-helix configuration. As the number of starts isincreased in the helix, the ends of the stent 1 begin to become moresquare-cut in appearance; for example, a triple-helix configurationwould have three “notches” at the end where the three loose ends arejoined to the adjacent turn. Because it is common to provide radiopaquemarkers at the ends of stents, these three notches are advantageouslocations for three markers, resulting in a symmetrical, even end to thestent 1.

Torsional Compliance and Torsional Fatigue Resistance

The greater number of struts 5 and bridges 8, 9 of the present inventionresult in the spreading of local forces and deflections brought about inuse to a larger number of features, so that these local deformations arespread over a larger number of deforming elements. As a result, eachelement is proportionately less deformed. It is understandable that astent with 1500 struts will more readily absorb deformation and inflexion and torsion than a stent with half as many struts, with anattendant reduction in localized loads and deformations to the vessel orother body lumen in which it is placed.

Torsional compliance in a helical stent is determined by the ability ofthe helical strand of struts 5 to lengthen and shorten. Hence, a longerstrand of more numerous struts 5 and their joining bending segments 7will be better able to absorb lengthening and shortening. The result is,for stents of a given radial compressive strength and outward force, aconfiguration with a greater number of short struts 5 that will be moreeasily torsioned than one with a smaller number of longer struts 5. Arelated result is that, because torsionally induced strains are reduced,any tendency toward fatigue failure caused by torsional motions in-vivois also reduced.

Flexibility and Bending Fatigue Resistance

In the same way as torsional flexibility and fatigue resistance isimproved by increasing the number of flexing elements, the flexural (orbending) flexibility and fatigue resistance are also improved. Bendingof a stent 1 causes adjacent turns or columns of struts 4 to be forcedeither toward each other (on the inside of a bend) or spread apart (onthe outside of the bend). Because connecting bridges 8 join adjacentturns or columns 4, the local deformations caused by stent bending arespread over the struts 5 and bending segments 7 (the 180-degree loopsthat join the ends of struts) between the connecting bridges 8. Thus,the more elements (struts 5 and bending segments 7) that exist betweenthe connecting bridges 8, the greater number of elements there are toabsorb the deformations caused by stent bending. Also, in aconfiguration with shorter struts 5, there is a greater number of turnsor columns 4 acted upon by bending the stent 1, so the total number ofelements deformed by bending the stent 1 is further increased, resultingin much smaller deformations to each of the elements. As deformationsare reduced and strut widths are reduced, the effective strains in thestent material are significantly reduced, resulting in much improvedfatigue resistance.

Enhanced Surface Area for Drug Elution

The large number of struts 5 of shorter length in a stent 1 madeaccording to the teachings of the present invention has greater surfacearea. For example, a stent 1 according to the present teachings willhave over twice as much kerf length than an otherwise similar prior artstent with half as many struts around the circumference. Inself-expanding stents, kerf area (the area of the cut radial faces ofthe stents elements) is the major contributor to total surface areabecause the area of the inner and outer surfaces is relatively smaller,due to the high aspect ratio (thickness to width) of the struts. Thus,the total surface area of a stent 1 made according to the presentteachings is substantially larger than that of a stent made according toprior-art configurations and, thus, it provides a larger surface area onwhich to apply medicated coatings. This larger surface area allowsvirtually all tissue within the coverage area of the stent to be in thedrug elution areas. In particular, the stent provides tissue coverage sothat no element of wall tissue is more than 350 microns to 400 micronsaway from the nearest strut. Such a configuration assures a shortdiffusion path from a strut covered with a drug-eluting agent to anyportion of the tissue.

1. A stent, comprising: struts joined together to form a series of helical turns and defining an outer circumferential cylinder of the stent in an expanded state of the stent, the struts having first and second curved strut portions connecting adjacent straight strut portions, the second curved strut portions extending farther from the straight strut portions than the first curved strut portions; and connecting bridges disposed between each of the series of helical turns, each connecting bridge having one bridge strut with first and second ends, the first bridge strut end connected directly to a second curved strut portion of one of the series of helical turns and the second bridge strut end connected directly to a second curved strut portion of an adjacent one of the series of helical turns, the connecting bridges having edges perpendicular to an axis of the stent, the connecting bridges being raised from the outer circumferential cylinder when the stent is in the expanded state.
 2. The stent according to claim 1, wherein a diameter of the stent between approximately 4 mm and approximately 8 mm.
 3. The stent according to claim 2, wherein said length is between approximately 25 mm and approximately 150 mm.
 4. The stent according to claim 1, wherein a length of the stent between approximately 25 mm and approximately 150 mm.
 5. The stent according to claim 1, wherein said struts are s-shaped.
 6. The stent according to claim 1, wherein: said stent has a non-expanded state; and said connecting bridges are circumferentially oriented in said expanded state.
 7. The stent according to claim 1, wherein: said stent has a non-expanded state; and said connecting bridges are circumferentially oriented in said non-expanded state and said expanded state.
 8. The stent according to claim 1, wherein: said turns define a helical gap between adjacent turns; and said connecting bridges connect said adjacent ones of said turns across said helical gap.
 9. A stent, comprising: struts joined together to form a series of helical turns and defining a circumference of the stent, the series of helical turns defining a helical gap between adjacent turns, the struts having first and second curved strut portions connecting adjacent straight strut portions, the second curved strut portions extending farther from the straight strut portions than the first curved strut portions; and connecting bridges connecting adjacent turns across the helical gap, each connecting bridge having one bridge strut with first and second ends, the first bridge strut end connected directly to a second curved strut portion of one of the series of helical turns and the second bridge strut end connected directly to a second curved strut portion of an adjacent one of the series of helical turns, the connecting bridges curved in a plane perpendicular to an axis of the stent, the connecting bridges being raised from the outer circumference of the stent when the stent is in an expanded state.
 10. The stent according to claim 9, wherein: a diameter of the stent between approximately 4 mm and approximately 8 mm; and a length of the stent between approximately 25 mm and approximately 150 mm.
 11. The stent according to claim 9, wherein: said stent has an expanded state; said struts define an outer circumferential cylinder in said expanded state; and said connecting bridges are raised from said outer circumferential cylinder when said stent is in said expanded state.
 12. The stent according to claim 9, wherein: said stent has a non-expanded state and an expanded state; and said connecting bridges are circumferentially oriented in said non-expanded state and said expanded state.
 13. The stent of claim 1, the second curved strut portions having a longitudinal offset relative to a space between adjacent turns defined by the first curved strut portions.
 14. The stent of claim 9, the second curved strut portions having a longitudinal offset relative to a space between adjacent turns defined by the first curved strut portions.
 15. The stent of claim 9, the first curved strut portions of adjacent turns not being connected to each other. 